Electrical impedance tomography to control electroporation

ABSTRACT

Images created by electrical impedance tomography (EIT) are used to adjust one or more electrical parameters and obtain a desired degree of electroporation of cells in tissue. The parameters include current, voltage and a combination thereof. The cells are subjected to conditions such that they become permeabilized but are preferably not subjected to conditions which result in irreversible pore formation and cell death. The electroporation can analyze cell membranes, diagnose tissues and the patient as well as to move materials into and out of cells in a controlled manner.

CROSS-REFERENCES

This application is a continuation-in-part of application Ser. No.09/358,510 filed Jul. 21, 1999 to which is claimed priority under 35 USC§120 and which application is incorporated herein by reference in itsentirety.

FIELD OF THE INVENTION

This invention relates to the field of electroporation and mass transferacross cell membranes in general and the transport of ions across a cellmembrane in particular.

BACKGROUND OF THE INVENTION

Electroporation is a technique that is used for introducing chemicalspecies into biological cells, and is performed by exposing the cells toan electric potential that traverses the cell membrane. While itsmechanism is not fully understood, electroporation is believed toinvolve the breakdown of the cell membrane lipid bilayer leading to theformation of transient or permanent pores in the membrane that permitthe chemical species to enter the cell by diffusion. The electricpotential is typically applied in pulses, and whether the pore formationis reversible or irreversible depends on such parameters as theamplitude, length, shape and repetition rate of the pulses, in additionto the type and development stage of the cell. As a method ofintroducing chemical species into cells, electroporation offers numerousadvantages: it is simple to use; it can be used to treat wholepopulations of cells simultaneously; it can be used to introduceessentially any macromolecule into a cell; it can be used with a widevariety of primary or established cell lines and is particularlyeffective with certain cell lines; and it can be used on bothprokaryotic and eukaryotic cells without major modifications oradaptations to cell type and origin. Electroporation is currently usedon cells in suspension or in culture, as well as cells in tissues andorgans.

Electroporation is currently performed by placing one or more cells, insuspension or in tissue, between two electrodes connected to a generatorthat emits pulses of a high-voltage electric field. The pore formation,or permealization, of the membrane occurs at the cell poles, which arethe sites on the cell membranes that directly face the electrodes andthus the sites at which the transmembrane potential is highest.Unfortunately, the degree of permealization occurring in electroporationvaries with the cell type and also varies among cells in a givenpopulation. Furthermore, since the procedure is performed in largepopulations of cells whose properties vary among the individual cells inthe population, the electroporation conditions can only be selected toaddress the average qualities of the cell population; the procedure ascurrently practiced cannot be adapted to the specific characteristics ofindividual cells. Of particular concern is that under certainconditions, the electrical potential is too low for a cell membrane tobecome permeabilized, while under other conditions electroporation caninduce irreversible pore formation and cell death. A high electricfield, for example, may thus produce an increase in transfectionefficiency in one portion of a cell population while causing cell deathin another. A further problem with known methods of electroporation isthat the efficiency of transfection by electroporation can at times below. In the case of DNA, for example, a large amount of DNA is needed inthe surrounding medium to achieve effective transformation of the cell.

Many of the problems identified above are a consequence of the fact thatthe process of electroporation in both individual cells and tissuescannot be controlled in real time. There are no means at present toascertain in real time when a cell enters a state of electroporation. Asa result, the outcome of an electroporation protocol can only bedetermined through the eventual consequences of the mass transferprocess and its effect on the cell. These occur long after the masstransfer under electroporation has taken place. These and otherdeficiencies of current methods of electroporation are addressed by thepresent invention.

Also relevant to the present invention are current techniques for thestudy and control of mass transfer across cell membranes. Knowledge ofmass transfer across cell membranes in nature, both in cells that arefunctioning normally and in diseased cells, is valuable in the study ofcertain diseases. In addition, the ability to modify and control masstransfer across cell membranes is a useful tool in conducting researchand therapy in modern biotechnology and medicine. The introduction orremoval of chemical species such as DNA or proteins from the cell tocontrol the function, physiology, or behavior of the cell providesvaluable information regarding both normal and abnormal physiologicalprocesses of the cell.

The most common method of effecting and studying mass transfer across acell membrane is to place the cell in contact with a solution thatcontains the compound that is to be transported across the membrane,either with or without electroporation. This bulk transfer method doesnot permit precise control or measurement of the mass transfer acrossthe membrane. The composition of the solution at specific sites is notknown and is variable. In addition, when an electric field is present,the local field intensity will vary from one point to another.Furthermore, the surface of the cell that is exposed to the solution isnot well defined. Cell surface areas vary among cells in a givenpopulation, and this leads to significant differences among the cells inthe amount of mass transfer. For these reasons, the amount of masstransfer achieved by bulk transfer processes is not uniform among cells,and the actual amount transferred for any particular cell cannot bedetermined.

Attempts made so far to overcome the limitations of bulk transfertechniques include techniques for treating individual cells that includeeither the mechanical injection (microinjection) of chemical compoundsthrough the cell membrane or electroporation with microelectrodes. Ininjection techniques, the membrane is penetrated with a needle todeliver a chemical agent, localizing the application of the chemicalagent to a small region close to the point of injection. This requiresmanipulation of the cell with the human hand, a technique that isdifficult to perform, labor-intensive, and not readily reproducible.Electroporation with microelectrodes suffers these problems as well asthe lack of any means to detect the onset of electroporation in anindividual cell. These problems are likewise addressed by the presentinvention.

SUMMARY OF THE INVENTION

Devices, systems and particular methods are disclosed which make itpossible to precisely monitor the movement of materials across a cellmembrane. The information gained from monitoring the movement ofmaterials across a cell membrane may be directly applied to deduceinformation with respect to the cell and/or its membrane. Alternatively,the information obtained from monitoring may be applied in order tocontrol the movement of materials across the cell membrane such as bycontrolling the application of electrical current. Devices and systemsof the invention make it possible to move charged molecules, and inparticular ionic species, across a cell membrane and precisely monitorthe occurrence of such. When carrying out electroporation using thedevices, systems and methods of the invention the information obtainedfrom monitoring the movement of the charged particles across the cellmembrane is used to control the process of mass transfer across a cellmembrane. Specifically, the system is used to obtain measurements andchanges in electrical impedance across a cell membrane while the masstransfer properties of the cell are changed by the application ofelectrical current. Thus, information obtained on electrical impedancechanges brought by the application of electrical current are used, inreal time, in order to control the movement of charged molecules acrossa cell membrane.

One aspect of the invention is a method comprising creating anelectrical charge differential between a first point and a second pointseparated from the first point by an electrically conductive mediumcomprising a biological cell. A first electrical parameter between thefirst and second points is then measured. A second electrical parameteris then adjusted based on the measuring of the first electricalparameter. The first electrical parameter may be any parameter such asone selected of the group consisting of current, voltage and electricalimpedance. The second electrical parameter may be any parameter (thesame as or different from the first electrical parameter) such as oneselected from the group consisting of current, voltage or a combinationof current and voltage.

In a preferred embodiment the method further includes placing a materialin the electrically conductive medium, and adjusting the secondelectrical parameter in order to move the material into the biologicalcell. The material placed within the electrically conducted medium maybe any material such as a pharmaceutically active compound or drug, anucleotide sequence, a fluorescent dye, or a crystal which isspecifically designed to effect the cell in a desired manner. Inaccordance with the method various conditions are adjusted so that theelectrical potential between the two points is sufficiently high so asto cause the cell to be permeabilized. However, the conditions betweenthe two points are further adjusted so that electroporation isreversible and as such does not cause cell death unless that is a resultspecifically being sought.

In another aspect of the invention the electroporation is not carriedout for the purpose of moving material into or out of a cell but ratherto analyze the cell or group of cells and provide information ordiagnosis of the tissue or individual which contains the tissue. Inaccordance with this method an electrical charge differential is createdbetween a first point and a second point separated from the first pointby an electrically conducted medium comprising a biological cell. Afirst electrical parameter is then measured between the first and secondpoints. The measuring of the first electrical parameter is then analyzedin order to determine a character of the cell and in particular acharacteristic of a membrane of the cell. The first electrical parametermay be any parameter and is preferably selected from the groupconsisting of current, voltage and electrical impedance. A secondelectrical parameter is preferably adjusted in a manner which effectsthe membrane of the cell or cells present in the medium and the secondelectrical parameter is any parameter but preferably selected fromcurrent, voltage or a combination of both.

Another aspect of the invention is the device which is preferablycomprised of a first electrode, a second electrode, a source ofelectricity which may later be connected to the electrodes but isoptionally present when the device is sold. The device further includesa means for hindering the flow of electrical current between the firstand second electrodes except for electrical current flow through adefined route. Further, the device includes a means for measuring anelectrical parameter such as current, voltage or electrical impedancethrough the defined route and a means for adjusting the source ofelectricity based on the measured electrical parameter. The means forhindering electrical current flow is preferably comprised of anon-conductive material and defined route comprised of one or moreopenings each with a diameter less than that of a biological cell sothat a cell can fit within the defined route and have a current flowthrough but preferably not around the cell.

The device and systems of the invention can be used within the method inorder to move a wide range of materials into or out of the biologicalcell in order to obtain a desired result. The process can be carried outon an individual cell, a group of cells, cells within a cell culture orwithin a living organism, e.g. cells within invertebrates andvertebrates including mammals as well as in plants. When carrying outthe process on a plurality of cells (e.g. a tissue) a process of imagingthe tissue and adjusting electrical current in real time based on imagesmay be used. An imaging technology which may be applied is electricalimpedance tomography (EIT). This technology relies on differences inbioelectrical attributes within the body or an organism (e.g. a human)to produce an image. In the method of the invention EIT images can beused in the same manner as the measuring step is used when the processis carried out on a single biological cell. In essence, the EITtechnology makes it possible to “see” the effect of increased electricalcurrent flow resulting from electroporation thereby providinginformation which can be used to precisely adjust the flow of electricalcurrent so that cell membranes are permeabilized while not permanentlydisrupted.

Another aspect of the invention is a method which comprises sending anelectrical current between a first point and a second point separated bythe first point by an electrically conductive medium comprising tissue.The tissue may be present within a living organism such as a vertebrateor invertebrate and specifically includes mammals and humans. After thecurrent is sent an image of the tissue is created wherein the image isbased on an electrical parameter such as the electrical impedance of thetissue. Using the image as a guide an electrical parameter is adjustedin order to obtain a desired degree of electroporation of biologicalcells in the tissue. Electroporation will change electrical impedanceand that change can be visualized on the image created. The electricalparameter adjusted may be any parameter such as current, voltage or acombination of both. In a preferred embodiment a material is placed inthe electrically conducted medium such as being injected into the tissueand the adjustment of the current is carried out, based on the image, ina manner so as to move the material into biological cells of the tissue.The image created is preferably an impedance image created from knowncurrent inputs and measured input voltage using a reconstructionalgorithm. The impedance image may be created from a known voltageinput, a measured current input, or combination of known voltage inputand measured current input.

A device for carrying out this method is another aspect of the inventionwhich device includes a means for creating an electrical current acrossan electrically conducted medium. The device further includes a meansfor analyzing a first electrical parameter of the electricallyconductive medium in order to create an image and a means for adjustinga second electrical parameter based on the image to obtain a desireddegree of electroporation of biological cells in the electricallyconductive medium. The first electrical parameter is preferablyelectrical impedance and the second electrical parameter is preferablyselected from the group consisting of current, voltage or a combinationof both. The current is preferably created by a plurality of electrodespositioned about an area of tissue upon which the electroporation is tobe carried out.

The present invention arises in part from the discovery that the onsetand extent of electroporation in a biological cell can be correlated tochanges in the electrical impedance (which term is used herein to meanthe ratio of current to voltage) of the biological cell or of aconductive medium that includes the biological cell. An increase in thecurrent-to-voltage ratio across a biological cell occurs when the cellmembrane becomes permeable due to pore formation or because of celldamage or other modes of cell membrane poration. Likewise, a decrease inthe current-to-voltage ratio through a flowing conductive fluid occurswhen the fluid draws a biological cell into the region between theelectrodes in a flow-through electric cell. Thus, by monitoring theimpedance of the biological cell or of an electrolyte solution in whichthe cell is suspended, one can detect the point in time in which poreformation in the cell membrane occurs, as well as the relative degree ofcell membrane permeability due to the pore formation. This informationcan then be used to establish that a given cell has in fact undergoneelectroporation, or to control the electroporation process by governingthe selection of the electrical parameters of the process e.g. thevoltage magnitude. This discovery is also useful in the simultaneouselectroporation of multitudes of cells in a cell culture or invertebrates, invertebrates or plants. Specific embodiments apply theinvention to mammals including humans. The process provides a directindication of the actual occurrence of electroporation and an indicationof the degree of electroporation averaged over all the cells beingsubjected to the process. The discovery is likewise useful in theelectroporation of biological tissue (masses of biological cells withcontiguous membranes) for the same reasons.

The benefits of this process include a high level of control over theonset and degree of electroporation, together with a more detailedknowledge of the occurrence and degree of permeability created inparticular individual cells or cell masses. When applied to individualcells or to a succession of individual cells, this process assures thatthe individual cells are indeed rendered permeable and are indeedtransformed by the introduction of chemical species. The process alsooffers the ability to increase the efficiency of electroporation byavoiding variations in the electrical environment that would destroysome cells while having an insufficient effect on others.

The invention can be understood by describing a simple embodiment whichinvolves the use of an electrical device or system in which a biologicalcell can be placed and that contains a barrier that directs the electriccurrent flow and hence the ion flow through a flow path that passesthrough the biological cell while permitting substantially no electriccurrent to bypass the biological cell. In some of these embodiments, theinvention involves the use of an apparatus containing twoliquid-retaining chambers separated by a barrier that is substantiallyimpermeable to an electric current. The barrier contains an opening thatis smaller than the biological cell such that the biological cell oncelodged in the opening will plug or close the opening. To achieveelectroporation, the biological cell is secured over the opening bymechanical, chemical and/or biochemical means, preferably in areversible manner so that the biological cell can later be removedwithout damage to the biological cell. Once the biological cell issecured over the opening, a voltage is imposed between the two chambersand across the biological cell residing in the opening. The passage ofcurrent between the chambers is thus restricted to a path passingthrough the opening and hence through the biological cell. By monitoringthe current-voltage relation in the electric cell, the onset ofelectroporation is detected and the degree of pore formation iscontrolled, to both assure that electroporation is occurring and toprevent excessive pore formation and cell death. The user is thusafforded a highly precise knowledge and control of the condition of andthe flux across the biological cell membrane.

In another series of embodiments, this invention is useful in thediffusive transport of chemical species into or out of a biologicalcell. In these embodiments, the cell is again divided into two chambersseparated by a barrier, and the biological cell is lodged across anopening in the barrier in such a manner that the passage of liquidaround the cell from one chamber to the other is substantiallyprevented. A liquid solution of the species to be introduced into thebiological cell is placed in one or both of the chambers. Theconcentration of the species in the solution differs from that in thecell (either higher or lower, depending on whether one seeks tointroduce or remove the species from the cell), or the concentration inone chamber differs from that in the other chamber.

In preferred methods of applying this invention to diffusive transport,the solutions in the two chambers differ in concentration such that thedriving force for the diffusive transport is between the two chambersthemselves rather than between the chambers and the interior of thebiological cell. Knowledge and controlled monitoring of theconcentrations in each of the two chambers on a periodic or continuousbasis as the diffusion proceeds, together with the precise knowledge ofthe dimensions of the opening, enables the user to precisely observe andcontrol the rate and amount of the species that enters the cell. Thediffusion time can be controlled by imposing stepwise changes in theconcentrations in either or both of the chambers, thereby imposing orremoving the concentration differential. An application of particularinterest is the combination of this type of diffusive transport of achemical species with controlled electroporation as described in thepreceding paragraph.

In addition to being useful in connection with electroporationtechnology the present invention can provide valuable informationrelating to a cell or group of cells or tissue containing a group ofcells by monitoring electrical impedance and thereby providinginformation regarding the integrity of a cell membrane. Specifically,measurements are carried out regarding the movement of charged particlesacross a cell membrane. These measurements are related to the amount ofelectrical current needed to carry out the diffusion across a cellmembrane. The information obtained can be analyzed directly or comparedto previous measurements of a same tissue or measurements carried out ondiseased or normal tissue thereby providing an indication of the amountof change which has occurred in the tissue being measured (based on anearlier measurement of the same tissues) or the amount of variancebetween the tissue being measured and tissue with impaired cellmembranes (e.g. diseased cells) or a normal cell or tissue. The methodis carried out in a manner similar to that used for conductingelectroporation. However, no material needs to be added to the mediumsurrounding the cells. The device is similar in that it is divided intotwo portions with a positive electrode on one side and a negativeelectrode on another side separated by a barrier with the cells beingpositioned along openings on the barrier in a manner which allows forthe passage of charged particles through the cell and through theopening in the barrier from one electrode to another. The barrierhinders or completely eliminates the flow of charged particles exceptthrough the openings. The measurement of electrical impedance betweenthe electrodes make it possible to distinguish between cells with anintact membrane and cells with impaired membranes. By more preciselycarrying out the measurements it is possible to make determinations withrespect to the integrity of a normal cell membrane relative to animpaired (e.g. diseased) cell membrane.

Each of the various embodiments of this invention may be used with twoor more (i.e. a plurality of) biological cells simultaneously, or cellmasses such as in tissue which may be in an animal or plant during theprocess. The apparatus described above can be adapted for use with twoor more biological cells by arranging the barrier such that the currentor diffusive transport will be restricted to a flow path that passesthrough all of the cells while preventing bypass around the cells. Afurther application of the concepts of this invention is theelectroporation of biological cells suspended in a flowing liquid.Electrodes are placed in fixed positions in the flow channel, and avoltage is imposed between the electrodes while current passing betweenthe electrodes is monitored. Biological cells entering the regionbetween the electrodes will lower the current, the impedance serving asan indication of the presence of one or more cells in the region, andoptionally also as a signal to initiate the application of a highervoltage sufficient to achieve electroporation.

A further application of the device, system and method of the inventionis the electroporation of biological cells present within a tissue whichtissue may be present within a living organism such as a mammal.Electrodes are placed in fixed positions within the tissue, and voltageis applied between the electrodes while current passing between theelectrodes is monitored. Biological cells with intact membranes in theregion between the electrodes will increase the electrical impedance.Accordingly, a measurement of the electrical impedance provides anindication of the presence of one or more cells in the region.Electroporation will decrease the measured amount of impedance. When theprocess is carried out on a tissue then the measurement of electricalimpedance is a statistical average of the cells present between theelectrodes.

Electroporation methodology of the invention can be carried out ontissue in a living organism using an imaging technology which makes itpossible to determine when (and preferably to some extent the degree)cell membranes are transformed so as to allow the flow of electricalcurrent through their membranes. The preferred imaging technology iselectrical impedance tomography (EIT) which provides a changing imagecreated from information on differences in bio-electrical attributes ofthe tissue being imaged. A typical EIT image is acquired by injectingelectrical currents into the body and measuring the resulting voltagesthrough an electrode array. An impedance image is then produced from theknown current inputs and the measured voltage data using areconstruction algorithm. EIT is particularly appropriate for theimplementation of the invention in tissue because it actually mapselectrical impedances. Therefore, the region of tissue that will undergoelectroporation and in which, consequently, the equivalent electricalimpedance of the cells will change will be imaged by EIT. The image isused to adjust the electrical parameters (e.g. flow of electricalcurrent) in a manner which allows electroporation to occur withoutdamaging cell membranes.

Among the advantages that this invention offers relative to the priorart are the ability to treat cells individually and to adapt thetreatment conditions to the needs of individual cells. In embodimentswhere voltage is applied, the monitoring of the impedance affords theuser knowledge of the presence or absence of pores and shows theprogress of the pore formation and whether irreversible pore formationthat might lead to cell death has occurred.

An advantage of the barrier-and-opening apparatus is the highsensitivity of the signal to noise ratio by virtue of its restriction ofthe current to a current flow path passing through the opening.

A still further advantage is the ability of the apparatus and method tobe integrated into an automated system whereby the condition of eachcell is monitored by instrumentation and individual cells are lodged inthe opening and then removed at times governed by the monitoredconditions.

An aspect of the invention is a method of controlling electroporation ofbiological cells in real time by adjusting an electrical parameter (e.g.voltage and/or current) applied to a system based on real timemeasurements of changes in current detected.

A feature of the invention is that the general concepts can be appliedto carry out electroporation on a cell, multiple cells, a tissue orareas of tissues in a living animal.

An advantage of the invention is that a precise amount ofelectroporation can be obtained and cell damage avoided by controllingany given electrical parameter (e.g. current and/or voltage) appliedbased on real time measurements of changes in current which relates tothe amount of electroporation being obtained.

Another advantage of the invention is that it can be used to transfectcells with nucleotide sequences without the need for packaging thesequences in a viral vector for delivery, thereby avoiding the cellularspecificities of such vectors.

Still other advantages are that the process can be carried outrelatively quickly with a relatively low degree of technical expertise.

Yet another advantage is that the process can be used to transfect cellswithout generating an immune response.

Still another advantage is that the process is not limited by the sizeof the DNA (i.e. the length of the DNA sequences) and the amount of DNAbrought into a cell can be controlled.

Another feature of the invention is that imaging technologies such asEIT can be used to detect changes in impedance in a volume of cells.

Another feature of the invention is that it can use EIT in order to mapimpedance of an area of tissue and thereby detect changes in cellimpedance in a volume of cells to adjust any given electrical parameter(e.g. current flow and/or voltage) to obtain desired electroporation.

These and further features, advantages and objects of the invention willbe better understood from the description that follows.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a cross section of a microdiffusion device useful in thepractice of the present invention for infusing a biological cell with achemical species without the assistance of an electrical current toeffect electroporation.

FIG. 2 is a cross section of a microelectroporation device useful in thepractice of the present invention for achieving pore formation in abiological cell, and optionally for infusing the cell with a chemicalspecies with the assistance of electroporation.

FIG. 3a is a longitudinal cross section of an electroporation device inaccordance with this invention, designed for a mobile suspension ofbiological cells. FIG. 3b is a transverse cross section of the deviceshown in FIG. 3a.

FIG. 4 is a plot of current vs. voltage in a series of electroporationexperiments conducted using a microelectroporation device of thestructure similar to that of FIG. 2.

FIGS. 5a, 5 b, 5 c, and 5 d are plots of current vs. voltage in afurther series of electroporation experiments conducted using amicroelectroporation device similar to that of FIG. 2.

FIG. 6a shows current flow around cells prior to electroporation andFIG. 6b shows electrical current flow through cells after (during)electroporation.

FIG. 7 shows a typical electrical impedance tomography (EIT) system foruse with the invention.

FIG. 8a is an image of current flow through cells with irreversibleelectroporation and FIG. 8b is an image of current flow through cellswith reversible electroporation.

FIG. 9 is a graphic schematic view of a finite element mesh showing acircular region of tissue bounded by electrodes (dark dots)—the domainhas two different impedances.

FIG. 10 schematically shows typical electrode configuration, measuredelectrical variables and equipotential lines in a circular domain havingan inclusion with a different electrical impedance.

FIG. 11 shows an actual image in the top left whereas the impedancemapping is shown in the bottom right which shows differential impedancemapping.

DESCRIPTION OF THE INVENTION AND SPECIFIC EMBODIMENTS

Before the present devices and methods including methods for carryingout electroporation are described, it is to be understood that thisinvention is not limited to particular methods and devices described, assuch may, of course, vary. It is also to be understood that theterminology used herein is for the purpose of describing particularembodiments only, and is not intended to be limiting, since the scope ofthe present invention will be limited only by the appended claims.

Where a range of values is provided, it is understood that eachintervening value, to the tenth of the unit of the lower limit unlessthe context clearly dictates otherwise, between the upper and lowerlimits of that range is also specifically disclosed. Each smaller rangebetween any stated value or intervening value in a stated range and anyother stated or intervening value in that stated range is encompassedwithin the invention. The upper and lower limits of these smaller rangesmay independently be included or excluded in the range, and each rangewhere either, neither or both limits are included in the smaller rangesis also encompassed within the invention, subject to any specificallyexcluded limit in the stated range. Where the stated range includes oneor both of the limits, ranges excluding either or both of those includedlimits are also included in the invention.

Unless defined otherwise, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this invention belongs. Although any methods andmaterials similar or equivalent to those described herein can be used inthe practice or testing of the present invention, the preferred methodsand materials are now described. All publications mentioned herein areincorporated herein by reference to disclose and describe the methodsand/or materials in connection with which the publications are cited.

It must be noted that as used herein and in the appended claims, thesingular forms “a”,“and”, and “the” include plural referents unless thecontext clearly dictates otherwise. Thus, for example, reference to “abiological cell” includes a plurality of such biological cells andreference to “an electrode” includes reference to one or more electrodesand equivalents thereof known to those skilled in the art, and so forth.

The publications discussed herein are provided solely for theirdisclosure prior to the filing date of the present application. Nothingherein is to be construed as an admission that the present invention isnot entitled to antedate such publication by virtue of prior invention.Further, the dates of publication provided may be different from theactual publication dates which may need to be independently confirmed.

DEFINITIONS

The term “electrode” is intended to mean any conductive material,preferably a metal, most preferably a non-corrosive metal that is usedto establish the flow of electrical current from that electrode toanother electrode. “Electrically conductive” means for transmittingelectrical current that can be referred to in any manner, e.g. currentor voltage. Electrodes are made of a variety of different electricallyconductive materials and may be alloys or pure metals such as copper,gold, platinum, steel, silver, silver chloride, and alloys thereof.Further, the electrode may be comprised of a non-metal that iselectrically conductive such as a silicon-based material used inconnection with microcircuits. Typical electrodes used in tissueelectroporation are preferably rod-shaped, flat plate-shaped or hollowneedle-shaped structures. Electrodes may be used to deliver electricalcurrent continuously or to deliver pulses. The electrodes may be veryapplication-specific and be comprised of parallel stainless steelplates, implanted wires, needle pairs and needle arrays. Those skilledin the art will design specific electrodes that are particularly usefulin connection with the desired results of obtaining electroporation inaccordance with the present invention.

The term “tissue” shall mean a plurality of cells. The cells may be ofthe same or of a number of different types. These cells are preferablyorganized to carry out a specific function. Tissue includes tissuepresent within a living organism as well as removed tissue and may referto in vivo or in vitro situations. Further, the tissue may be from anyorganism including plants and animals or a tissue developed usinggenetic engineering and thus be from an artificial source. In oneembodiment the tissue is a plurality of cells present within a distinctarea of a human.

The terms “device” and “electroporation device” are used interchangeablyhere for describing any a device as disclosed and described throughout.The device preferably includes a first electrode and a second electrodewherein the first and second electrodes are connected to a source ofelectricity in a manner so as to provide the electrodes with positiveand negative charges respectively. The device also preferably includes ameans for hindering the flow of electricity between the two electrodesexcept through one or more specific openings. For example the means forhindering flow can be non-conductive material which has one or moreopenings therein wherein the openings are designed so as to specificallyhold a biological cell or group of biological cells. Thereby theelectrical current must flow through the opening and through the cellsto the other electrode. The device also preferably includes a means formeasuring the flow of electrical current between the electrodes. Themeans for measuring can include a volt meter, amp meter or any deviceknown to those skilled in the art which is capable of measuring the flowof electrical current in any manner. Further, the device preferablyincludes a means for adjusting the amount of electrical current flowbetween the electrodes. Thereby the voltage, current or other desiredparameter of electrical current flow can be specifically adjusted basedon the measured flow so as to obtain optimum electroporation of the cellor cells positioned between the electrodes. When the term“electroporation” is used it does not necessarily mean that the deviceis being used in order to move a compound such as a drug or DNA sequenceinto a cell.

The terms “power source”,“source of electricity” and the like, are usedinterchangeably herein to describe any means for providing electricalpower, current or voltage thereby creating a flow of electrical currentbetween the electrodes. The device preferably is capable of providingfor a controlled mode and amplitude and may provide constant DC currentor AC current, provide pulse voltage or continuous voltage. Preferreddevices are capable of exponentially decaying voltage, ramp voltage,ramped current, or any other combination. For example, a power supplymay be used in combination with a chip of the type used in connectionwith microprocessors and provide for high-speed power amplification inconnection with a conventional wall circuit providing alternatingcurrent at 110 volts. The pulse shape may be generated by amicroprocessor device such as a Toshiba laptop running on a LabViewprogram with output fed into a power amplifier. A wide range ofdifferent commercially-available power supplies can provide the desiredfunction. The electrical potential delivered for electroporation isusually quoted in terms of the voltage gradients that develop in theaffected region that is defined in units of V/cm developed in thetissue. Ranges include a range of 10 V/cm to 100,000 V/cm or morepreferably 100 V/cm to 10,000 V/cm. However, the range isamplification-specific and can be extended outside the range for anydesired application. Electrical pulses range from microseconds tomilliseconds in general. However, other ranges of pulsing may beutilized depending on the desired results.

INVENTION IN GENERAL

While this invention extends to a variety of structures, methods, andapplications, this portion of the specification will illustrate certainspecific structures and methods in detail, from which the concepts ofthe invention as a whole will become apparent.

A wide range of different devices and system can be used to carry outthe method of the invention. The device must be comprised of a firstelectrode having a first voltage and a second electrode having a secondvoltage. Further, the device will comprise a means for detecting chargedparticle flow between electrodes and a means for varying the electricalcurrent between electrodes based on data obtained by detecting changesin charged particle flow between electrodes. Preferably the device isfurther comprised of a component that prevents or substantially reducescharged particle flow between electrodes except for flow occurringthrough one or more biological cells positioned between the first andsecond electrodes.

Any desired material can be added to the medium in order to move thatmaterial into a cell which is present in the medium. Further, theinvention does not necessarily include a process step of including amaterial into the medium which is to be brought into a cell. The processcan be carried out merely to determine changes which occur in a cellmembrane based on the electrical current applied. That information canbe valuable to determine characteristics about the cell or group ofcells present in the medium and, specifically, can be used to comparewith information on normal and diseased cells or to determine thedifferences between previously tested cells and those currently beingtested.

The first structure that will be discussed is an electroporation cellwith an internal support to hold a single biological cell and aninternal barrier that restricts the electric current flow in theelectric cell to a flow path that passes through the biological cell.When no voltage is applied, the structure can be used for diffusivetransport alone, unassisted by voltage-induced pore formation.

The configuration of the barrier, and the two chambers in embodimentsthat include two chambers, is not critical to the invention, and canvary widely while still serving the purposes and advantages of theinvention. Since biological cells are microscopic in size, however, thepreferred type of apparatus for the practice of this invention in eachof its various forms is one in which the structure as a whole and/or itschambers are the size of electronic chips, fabricated bymicrofabrication techniques such as those used in electronic chipmanufacture. It is further preferred that the chambers are constructedas flow-through chambers to allow the passage of the liquids incontinuous flow, intermittent flow, or flow at the direction of theuser, and to allow changes in the concentrations, pressure, and otherconditions as needed to achieve close control over the passage ofspecies across the biological cell membrane. Accordingly, a preferredstructure and method of manufacture of the apparatus are those thatinvolve the formation of the apparatus in layers or platelets withappropriate openings that form flow passages when the layers orplatelets are bonded together.

Flow-through chambers offer the advantage of permitting the successiveentry and removal of individual cells so that large numbers of cells canbe treated in succession. Flow-through chambers also permitreplenishment of solute-depleted solutions so that concentrationgradients can be continuously maintained when desired. A furtherfunction that can be served by flow-through chambers is the increase anddecrease of pressure, a function that is useful for various purposes asdescribed below.

The support for the biological cell in this structure can be anystructure that secures the biological cell in a fixed position and thatallows the passage of electric current. The most convenient support isan opening in the barrier. Securement of a biological cell over theopening serves to close, seal or plug the opening, thereby directing thepassage of electric current, diffusive transport, or both, through thecell and eliminating or minimizing leakage around the cell. A convenientmechanical means of achieving this is to impose a pressure differentialacross the opening in a direction that will press the cell against theopening. The diameter of the opening will be smaller than that of thecell, and the cell upon entering the apparatus will pass into one of thetwo chambers. By increasing the pressure in the chamber in which thecell resides, or lowering the pressure in the other chamber, the cellwill be forced against the opening, closing it off. Once the procedureis completed, the cell is readily released from the opening byequalizing the pressures in the two chambers or by reversing thedifferential such that the higher pressure is in the chamber other thanthe chamber in which the cell was introduced. The flow of liquid in thechamber in which the cell was introduced will then remove the cell fromthe opening, exposing the opening for another cell.

An alternative method of sealing the opening with the cell is by the useof a coating on the barrier surface, or over the rim of the opening, ofa substance that binds to the cell membrane. Since biological cellmembranes are negatively charged, the coating may be a substance thatbears a positive charge, such as polylysine, polyarginine, orpolyhistidine. The biological cell can be directed to the opening by apressure differential across the opening, and held in place by thecoating. Once the procedure is completed, the cell can be released fromthe coating by momentarily increasing the flow rate of the liquid in thechamber on the cell side of the opening, or by imposing a reversepressure differential across the opening to urge the cell away from theopening.

The size of the opening is not critical to the invention provided thatthe opening exposes sufficient surface area on the cell membrane toachieve the desired degree of either mass transfer, the passage of anelectric current, or both, within a controllable and economicallyreasonable period of time. The optimal size will thus vary with theparticular cells being treated or studied. In general, the opening ispreferably circular or approximately circular in shape, and depending onthe cell size, preferably ranges in diameter from about 1 micron toabout 100 microns, more preferably from about 1 micron to about 50microns, and most preferably from about 2 microns to about 20 microns.The barrier in which the hole is formed and which separates the twochambers is preferably of a rigid dielectric material that isimpermeable to both water and solutes and that will hold a pressuredifferential sufficient to secure a cell against the opening. Fordevices that are manufactured by microfabrication techniques, aconvenient material for the barrier is silicon nitride. Other materialsthat will serve equally well will be readily apparent to those skilledin the art.

A further feature of preferred embodiments of this invention is the useof apparatus made of transparent materials. This enables the user toobserve cell interiors and the processes of microdiffusion andmicroelectroporation through a microscope as they occur.

ELECTROPORATION USED IN IN VIVO THERAPY

The electroporation techniques of the present invention are useful inconnection with treating, analyzing or diagnosing an organism includingmammals and humans in need of treatment. In general, treatment may becarried out by injecting a material continuously or in a rapid bolusinto an area of tissue to be treated. Electrodes are placed adjacent tothe tissue and current or voltage are applied and measured continuouslyin order to determine when the desired level of electroporation isobtained thereby making it possible to move the injected material intothe cells of the tissue being treated.

The pharmaceutically active compound that is injected may be aconventional drug normally referred to as a small molecule or be aprotein or nucleotide sequence that encodes a protein. Further, thecomposition injected into the tissue may be administered before, duringor even after the application of electrical pulses from theelectroporation device. The overall goal of the process is to providefor the opening of pores via electroporation and thereby introduce thecompounds into the cells which compounds would not normally penetratethe cell membrane. For example, it is possible to introduce bleomicyn orvarious gene constructs and/or plasmids into cells of the tissue beingtreated. This is accomplished by generating electrical potentials andcurrents across the cells within the tissue to treated wherein theelectrical potentials are generated as electrical pulses. It ispreferable to utilize a plurality of electrodes as opposed to a singleelectrode in order to generate the pulses.

An example of a useful electrode design is one that is comprised of twoflat steel strips 10 mm in width and 0.6 mm in thickness. The electrodesare spaced at a fixed distance of approximately 6 to 7 mm from eachother. A second electrode design is comprised of two to as much as eightflat steel squares of 20 mm. The electrodes are connected to a PS15electropulsator. Pulses can be delivered by placing the electrodes onthe skin with the flat side on the skin or by placing the electrodesaround skin tumors. Skin contact can be achieved by the use of materialsconventionally used in connection with performing electrocardiographssuch as electro-conductive gels or saline. In order to carry out theprocedure a patient can receive one or a plurality of pulses andpreferably receives a plurality of pulses. Different configurations canbe designed in order to carry out electroporation of tissue inside anorganism such as inside a human body, i.e. without applying electrodesoutside the skin. Such configurations can be comprised of needle arraysthat comprise a plurality of needle electrodes. As an example thepositive and negative electrodes can each be comprised of six or moreneedles that are 0.5 mm in diameter and comprised of stainless steel, 1cm in length connected to a BTX 820 pulse generator. The electrodes canbe inserted in parallel into the tissue around the cells to be affectedby electroporation. The electrodes can be positioned in circles ofvarious diameters ranging from 5 mm to 1 cm. Voltage electrode ratio inthe range of approximately 1300 V/cm can be used. Although any number ofpulses can be delivered it is preferable to begin the process bydelivering approximately six pulses in one second intervals with a pulsewidth of 100 microseconds. The present invention is particularlydesirable in connection with electroporation of tissue in that themethod can determine whether electroporation is occurring without theuse of dyes and tags in order to track the material being brought insidethe cell.

As shown in FIGS. 6a and 6 b the electrical current can flow around thecells (FIG. 6a) or through the cells (FIG. 6b) after electroporation hastaken place. The process of the invention makes it possible to determinethe point when the transition is occurring between what is shown in FIG.6a and what is occurring in FIG. 6b and further makes it possible toprevent the occurrence of irreversible effects on the cell membranes. Asshown in FIG. 8a the electroporation can be carried out to such a greatextent that cell membranes are damaged thereby resulting in irreversibleeffects on the cells. In general, this is undesirable. However, bymodulating the amount of electrical current it is possible to obtainelectroporation without significant damage to the cell membranes therebyobtaining a reversible situation as shown in FIG. 8b.

As shown in FIGS. 6a and 6 b cells create electrical impedance and thepresent invention relates to precisely determining the degree of thatelectrical impedance and adjusting current so as to obtain desiredresults with respect to electroporation. However, when large numbers ofcells are involved such as in a tissue it may be desirable to use othermechanisms for measuring other effects of the current in creatingelectroporation on a plurality of cells in the tissue. Electricalimpedance is a measurement of how electricity travels through a givenmaterial. Every material has a different electrical impedance determinedby it's electrical composition. Some materials have high electricalimpedance and others have low electrical impedance. Breast tissue whichis malignant (cancerous) has much lower electrical impedance (conductselectricity much better) than normal tissue or a benign (non-cancerous)tumor.

Impedance is a measurement of the degree to which an electrical circuitresists electrical-current flow when voltage is impressed across itsterminals. Impedance expressed in OHMS, is the ratio of the voltageimpressed across a pair of terminals to the current flow between thoseterminals. In direct-current (DC) circuits, impedance corresponds toresistance. In alternating current (AC) circuits, impedance is afunction of resistance, inductance, and capacitance. Inductors andcapacitors build up voltages that oppose the flow of current. Thisopposition is referred to as reactance, and must be combined withresistance to define the impedance. The resistance produced byinductance is proportional to the frequency of the alternating current,whereas the reactance produced by capacitance is inversely proportionedto the frequency.

The basic concepts described above are utilized in the basic aspects ofthe present invention and are also applicable to describing electricalimpedance imaging also referred to as electrical impedance tomography(EIT). It should be noted that a number of different terminologies maybe used to describe the same technique and those include appliedpotential tomography (APT). These imaging technologies make it possibleto produce images based on the spatial variation of the electricalproperties of the biological tissue. Techniques such as APT and EITcould be utilized to carry out the invention in connection with tissue.The applied potential tomography (APT) relies for its physical basis onthe measurement of a potential distribution on a surface of a biologicalmaterial, when an electrical current is applied between two points ofits surface. Other researchers have utilized the technique and referredto it as electrical impedance imaging, conductivity imaging, electricalimpedance tomography, etc. Herein, the technology is generally referredto as EIT or electrical impedance tomography. Accordingly, within theremainder of the disclosure the technology is referred to only as EITtechnology and an example of such is shown within Example 3 below.

Those skilled in the art will contemplate different means of determiningchanges in electrical current upon reading this disclosure. A preferredmethod for determining such when carrying out the invention on tissue isto use imaging technology and specifically electrical impedancetomography (EIT) which monitors and analyzes differences inbio-electrical attributes of the sample being monitored in order toproduce an image. The EIT technology can be used in connection with thepresent invention by creating an EIT image and using that image toadjust current flow to obtain desired results. Specifically, the EITimage is created by injecting electrical currents into the tissue andmeasuring the resulting voltages through an electrode array. This makesit possible to produce an impedance image from the known current inputsand the measured input voltage data using a reconstruction algorithm.The use of EIT technology is particularly desirable in connection withthe present invention as applied to tissue in that EIT imaging providesa map of electrical impedances. The map of electrical impedancesessentially allows the user to visualize when electroporation isbeginning. When electroporation begins the user can stabilize the amountof current being applied and thereby avoid applying so much current asto result in irreversible damage to cells as shown in FIG. 8a. The EITtechnology makes it possible for the region of tissue undergoingelectroporation to be visualized based on changes in equivalentelectrical impedance of the cells within tissue being monitored.

FIG. 7 shows a conceptual view of an EIT system being used to carry outa process of the present invention on tissue 71. A current source 72 iscontrolled by a signal generator 73 and is used to drive an electricalcurrent into the tissue sample 71 through a pair of computer controlledmultiplexers 74 and 75 which lead to a differential amplifier 76 anddemodulator 77. The measured signals are compared to the original inorder to record amplitude and phase data for later image construction.The controlling computer 78 typically chooses which pair of electrodeswill inject current while reading the remaining electrode voltages.There are a number of different hardware configurations which can beutilized in connection with the present invention.

The EIT system as shown in FIG. 7 is generally referred to as a serialsystem because of it's single current source and measurement amplifier.Varying degrees of parallelism (multiple current sources and voltagemeasuring amplifiers) have been utilized in other systems therebyincreasing the flexibility and speed of the current injection system.

Reconstruction algorithms are used in order to take the voltage measuredon an outer surface of a region of interest in the body (the injectedcurrent data) and information relating to the electrode geometry, andproduce an image which represents spatial tissue impedance tissuedistribution inside the region of the tissue 71. There are a number ofmethods which can be used to create an impedance image. Static imagingis the production of an absolute impedance distribution. Cook, R. D. etal. ACT3: a high speed, high precision electrical impedance tomography.IEEE, Trans. Biomed. Eng. 41, 713-22 (1994). Differential imagingmethods produced distributions based on differences between two datasets. Barber, D. C. in Advances in Biomed Eng. (ed. Benek in, W.,Thevenin, V.) 165-173 (IOS Press, Amsterdam, 1995). This type oftechnique provides an image of how the impedance distribution haschanged from one baseline measurement. Multi frequency impedance imagingtakes advantage of the frequency dependence of tissue impedance.Groffiths, H. The importance of phase measurement in electricalimpedance tomography. Physics in Medicine and Biology 32, 1435-44(1987). Quasi-static images can be produced using the above differentialtechnique with a low frequency image used as the baseline. Accordinglythe system makes it possible to produce a type of static imaging withoutthe difficulties of true static imaging.

In order to provide for reconstruction and thus and image, amathematical model of how the current behaves in the tissue is used. Ingeneral a model governing current flow in EIT is provided by thewell-known Poisson equation. The type of mathematical analysis that isneeded in EIT image reconstruction as well as many other medical imagingtechnologies, belongs to a general class known as boundary valueproblems. There are a number of different methods of solving boundaryvalue problems. However, these problems can all be classified intoeither analytical or numerical iterative techniques and those skilled inthe art can apply such in order to carry out the present invention.

The vast majority of reconstruction algorithms currently in use employiterative numerical solutions to the Poisson equation. Most iterativenumerical approaches attempt to solve the boundary value problem byguessing an impedance distribution in the tissue and repeatedly solvingthe forward problem (finding the voltage and current densities given animpedance distribution) and adjusting the impedance guessescorrespondingly, until the voltage and currents measured fit thosecalculated. The forward problem must be solved numerically and isusually done so using finite element or finite difference schemes. TheFEM is a very powerful and popular method of forward problem solution,and because of this, tends to dominate engineering solutions across manyinterdisciplinary fields.

An example of a microdiffusion apparatus in accordance with thisinvention for a single biological cell, for transporting materialsacross the cell membrane without the application of an electric field,is shown in FIG. 1. This components of this apparatus, from the bottomup, are an acrylic base 11, an intermediate silicon layer 12 (1 micronin thickness) with a portion 13 carved out to define the lateralboundaries of the lower of the two liquid chambers, a silicon nitridelayer 14 serving as the barrier between the two chambers, a siliconwasher 15 defining the lateral boundaries of the upper liquid chamber16, and a glass cover plate 17. A hole 18 in the silicon nitride barrierserves as the opening, and a cell or contiguous cell mass such as tissue19 is shown covering the hole. Channels extend through the acrylic baseto serve as inlet and outlet channels for the liquids that pass throughthe upper and lower chambers, as shown by the arrows in the Figure.

When the pressure in the upper chamber 16 is higher than that in thelower chamber 13, the cell will be retained in position over the hole,serving as a plug separating the liquids in the two chambers from eachother. When the composition of the solutions in the two chambers differsfrom that of the cell interior, mass transfer occurs across the cellmembrane between the chambers and the cell. When the composition of thesolution in one chamber differs from that in the other, mass transferoccurs through the cell from one chamber to the other. By preciselycontrolling the compositions of the solutions in the two chambers, onecan precisely control the mass transfer rate and direction within thecell. Since the diameter of the opening 18 is known, one can preciselydetermine the mass transfer that occurs through the opening.

The numerous applications of this microdiffusion device will be readilyapparent. For example, the device can be used to infuse a cell with acryopreservative such as glycerol by filling the upper chamber 16 withphysiological saline and the lower chamber 13 with glycerol. When usinga cell 19 for which the mass transfer coefficient of glycerol across thecell membrane is known, one can readily calculate the amount of glycerolthat will enter the cell and adjust the concentrations and exposuretimes to infuse the cell with the amount that is known to be requiredfor cryopreservation.

An example of a microelectroporation apparatus in accordance with thisinvention for a single biological cell, is shown in FIG. 2. Theapparatus is similar in construction to the microdiffusion apparatus ofFIG. 1. Its structural components, from the bottom up, are an acrylicbase 21, a lower silicon layer 22 with a portion carved out to definethe lateral boundaries of the lower liquid chamber 23, a silicon nitridelayer 24 (1 micron in thickness) serving as the barrier between the twochambers, an upper silicon layer 25 defining the lateral boundaries ofthe upper liquid chamber 26, and a cover consisting of an n+poly-silicon layer (5,000 Å in thickness) 27 and a silicon nitride layer(1 micron in thickness) 28. A hole 29 in the silicon nitride barrier 24serves as the opening, and a cell 30 (or cell mass) covers the hole.Channels extend through the acrylic base to serve as inlets and outletsfor the liquids that pass through the upper and lower chambers, as shownby the arrows in the Figure. A further layer of n+ poly-silicon (5,000Å) 31 resides above the acrylic base 21, and this layer, together withn+ poly-silicon layer 27 above the upper chamber 26 serve as the twoelectrodes. Each electrode is joined by electric leads to a printedcircuit board 32 which controls the voltage applied between theelectrodes and measures the current passing between them.

The microelectroporation apparatus shown in FIG. 2 can be fabricated byconventional microfabrication techniques, typically involving chemicalvapor deposition, masking, etching and sputtering. The operation of theapparatus will be analogous to the operation of the microdiffusionapparatus of FIG. 1. The movement of biological cells through theapparatus is achieved by suspending the cells in the liquid used to fillthe upper chamber, and cells are drawn to the opening, one at a time, byimposing a pressure differential between the chambers, which also holdsa cell in place once the cell has been drawn to the opening. Aconvenient method of imposing such a pressure differential is tomaintain atmospheric pressure in the upper chamber while lowering thepressure in the lower chamber below atmospheric by attaching a syringeto the lower chamber and pulling on the syringe plunger. Care should betaken to limit the pressure differential to one that will not damage thecell.

FIGS. 3a and 3 b illustrate to a different apparatus and method withinthe scope of this invention. This apparatus and method involve a fluidsuspension of biological cells flowing through a conduit or flowchannel, in which the cells pass through a region between a pair ofelectrodes. The longitudinal cross section of FIG. 3a shows the walls 41of the channel, and a biological cell 42 passing downward through thelumen of the channel (in the direction of the arrow). The transversecross section of FIG. 3b shows that the channel is rectangular in crosssection, although other cross-sectional geometries may be used.Electrodes 43, 44 are formed as coatings on two opposing walls of thechannel. The electrodes are connected through leads to a printed circuitboard 45 which measures the impedance and controls the voltage appliedto the electrodes. The biological cell 42 is shown passing through theregion between the two electrodes.

The area of the cross section of the channel is large enough to permitthe cell to pass through essentially unimpeded by the channel walls, andyet small enough that only one cell can pass through the inter-electroderegion at a time. In addition, each electrode 43, 44 is eitherapproximately equal in length or slightly larger in length than thediameter of the biological cell, so that the cell upon entering theregion causes a significant or measurable decrease in the currentpassing through the region due to the voltage applied across electrodes.The spacing of the electrodes, i.e., the distance between them, islikewise subject to the same considerations. The biological cells aresuspended in a liquid solution of the species to be introduced into thecells, and the suspension is passed through the channel. A voltage isapplied between the electrodes as suspension flows through the channel,and the current between the electrodes (or the impedance) is monitored.A significant drop in the current indicates the presence of a biologicalcell in the inter-electrode region. Once the cell is detected in thismanner, an electroporation pulse can be applied to the electrodes whilethe cell is still in the inter-electrode region, and impedance can beobserved further to detect the onset of electroporation. The speciesdissolved in the liquid solution will enter the cell as a result of theelectroporation.

Variations on these structures and methods will be readily apparent tothose skilled in the art. For example, the barriers described above canbe minimized or avoided by using microelectrodes that are the same sizeas or smaller than the biological cells. Examples of suchmicroelectrodes are carbon fiber microelectrodes (such as ProCFE, AxonInstruments, Foster City, Calif., USA) used in conjunction withhigh-graduation micromanipulators (such as those available fromNarishige MWH-3, Tokyo, Japan). Microelectrodes can be used in place ofthe electrodes shown in FIG. 2 or in place of those shown in FIGS. 3aand 3 b.

EXAMPLES

The following examples are put forth so as to provide those of ordinaryskill in the art with a complete disclosure and description of how tomake and use the present invention, and are not intended to limit thescope of what the inventors regard as their invention nor are theyintended to represent that the experiments below are all or the onlyexperiments performed. Efforts have been made to ensure accuracy withrespect to numbers used (e.g. amounts, temperature, etc.) but someexperimental errors and deviations should be accounted for. Unlessindicated otherwise, parts are parts by weight, molecular weight isweight average molecular weight, temperature is in degrees Centigrade,and pressure is at or near atmospheric.

Example 1

A series of experiments was performed using a microelectroporationsystem consisting of the microelectroporation device described above andshown in FIG. 2, combined with flow and pressure control units andpressure gauges for the liquids to be circulated through the upper andlower chambers, a variable DC power supply, a pulse generator and poweramplifier for imposing voltage pulses across the device, a digitaloscilloscope for monitoring the pulses, a fluorescent microscope, a CCD(charge coupled device) camera, and a computer with image processing andwaveform processing software. Both chambers of the device were filledwith physiological saline and cells were introduced into the upperchamber. Liquid motion in the top and bottom chambers was controlled bysyringes. The pressure in the upper chamber was atmospheric while thepressure in the lower chamber was reduced below atmospheric by pullingon the barrel of the syringe connected to that chamber. The voltage wasapplied in single square pulses ranging from zero to 120V in magnitudeand from 2 microseconds to 100 milliseconds in duration. The distancebetween the electrodes in the upper and lower chambers was 900 microns.

The tests in this example were performed using ND-1 human prostateadenocarcinoma cells with a typical diameter of 20 microns. The openingin the microelectroporation device was 5 microns in diameter. Arectangular voltage pulse was applied with a duration of 60milliseconds, and the pulse was applied at various amplitudes rangingfrom 10V to 60V in increments of 5 volts. With each pulse, the electriccurrent passing through the opening was measured. Experiments wereperformed with the cells and were repeated both with the opening stoppedby a glass bead and with no obstruction at all in the opening. Theresults in each case were expressed as microamperes of current vs. voltsof pulse amplitude and are plotted in FIG. 4, in which the upper curve(data points represented by x's) represents the unobstructed opening,the lower curve (data points represented by asterisks) represents thedata taken with the glass bead residing in the opening, and the threemiddle curves (open squares, open upright triangles, and open invertedtriangles) represent data taken with three different ND-1 cells residingin the opening.

The upper curve shows that the current increases in a substantiallysteady manner as the voltage increases when there is no barrier to thepassage of current through the opening. The lower curve also shows asubstantially steady rise as the voltage increases, although at a muchlower level. The current values shown in the lower curve represent straycurrents through the device. The curves of data taken with the ND-1cells across the opening show that at low voltages the current is closein value to that obtained when the opening is closed by the glass beadwhile at high voltages the current rises to the levels obtained with anunobstructed opening. The transition is a sharp increase which isindicative of the formation of pores in the cell membrane through whichan electric current can pass, i.e., the onset of electroporation. In allthree cells, the transition occurred at voltages between 30V and 40V. Intwo of the three cells (open squares and open upright triangles), theonset of electroporation occurred essentially at the same voltage, whilein the third (inverted triangles), the onset occurred at a voltage thatwas lower than the other two by about 5V. This illustrates the value ofcontrolling the process for individual cells to achieve optimal results.

After the data shown in FIG. 4 was generated, the pulses were reappliedin descending order of amplitude values, and the resulting curvesdisplayed hysteresis, i.e., the curves obtained with descendingamplitudes were higher in voltage than those obtained with ascendingamplitudes. This indicated that the electroporation in these experimentswas irreversible.

Example 2

Using the same microelectroporation system used in Example 1, a seriesof tests were performed on rat hepatocytes (ATCC #CRL-1439), whosetypical cell diameter was 20 microns, the microelectroporation apparatushaving an opening that was 4 microns in diameter. Here as well,rectangular voltage pulses that were 60 milliseconds in duration wereused, ranging in amplitude from 10V to 37.5V in increments of 5V in theportion from 10V to 30V and in increments of 2.5V in the portion from30V to 37.5V. The experiments were performed in some cases only byincreasing the amplitudes and in others by first increasing, thendecreasing the amplitudes to evaluate reversibility. The results areplotted in the graphs shown in FIGS. 5a, 5 b, 5 c, and 5 d. In eachcase, the upper curve (data points represented by circles) is the datataken with neither a cell nor a glass bead residing in the opening, thelower curve (data points represented by squares) is the data taken witha glass bead in the opening, and the middle curve (data pointsrepresented by triangles) is the data taken with a hepatocyte in theopening, using different hepatocytes for each of the four Figures.

In FIG. 5a, the amplitude was increased and not decreased, displaying anelectroporation threshold voltage of between 25V and 30V. In FIGS. 5band 5 c, the amplitude was first increased and then decreased to producethe two middle curves. Although the ascending and descending curves arenot differentiated, they are substantially identical in each Figure,indicating that the cell membrane in each of these two cases resealedafter each voltage pulse and thus that the pore formation wasreversible. In the test represented by FIG. 5d, the cell disintegratedonce the applied voltage exceeded 37.5V, although this is not shown inthe Figure. It is significant to note that despite the fact that thesame cell types were used in each of FIGS. 5a, 5 b, 5 c, and 5 d, theelectroporation threshold voltage differed among the individual cells,although all were within the range of 20V to 35V. Adaptation of theprocedure to individual cells is readily achieved by monitoring thecurrent in this manner to note when the electroporation thresholdoccurs. Selection of the optimal exposure time, voltage, compositionchanges in the surrounding liquids, and other parameters of the systemcan then be made to achieve the desired treatment of the cell withoutdestruction of the cell.

The methods described herein are useful tools in the laboratory forconducting fundamental research in the electroporation properties ofbiological cells, and useful tools in industry for processing largequantities of cells in a flow-through manner. By enabling one to observeand record the current flowing through individual cells, one can controlthe amplitude and duration of the voltage pulse to achieve optimalresults. In addition, the devices described and shown herein for use inpracticing the invention can be constructed with transparent parts andof a size suitable for mounting on a microscope stage. This will permitone to correlate the electrical current measurements to visualobservations and fluorescence measurements inside the cell. The devicecan be used to electrically detect, through the measurement of currents,the point in time when a cell becomes lodged in the opening as well asthe point in time when pore formation is achieved in the cell membrane.For larger scale and industrial applications, large numbers ofmicroelectroporation devices of the type described herein can bearranged in parallel. For each cell, electrical information indicatingthe trapping of a cell in the opening (such as a sharp drop in thecurrent) can be used to generate a signal that will initiate anelectroporation sequence, and further electrical information indicatingthe completion of electroporation (such as a sharp rise in current) willgenerate a signal that will release the cell (for example by eliminatingor reversing the pressure differential) and permit the next cell to flowtoward the opening.

In addition to using the device and system of the invention to move amaterial into or out of the cell the system and device can be used in adiagnostic or analytic mode. This is carried out by measuring electricalimpedance of a cell or cells placed in a medium and using the measuredelectrical impedance information. It is possible to deduce informationrelating to the integrity of cell membranes and thus provide foranalysis. It is also possible to compare the information to informationpreviously obtained on normal or diseased cells of the same type andthereby obtain diagnostic information. For example, the electricalimpedance of a cell with an intact membrane will be much high than theimpedance of the same cell with impaired membrane. Thus, analyticallythe process can provide information with respect to the structuralintegrity of the cell membrane. Diagnostically the method can provideinformation with respect to the relative structural integrity of cellmembranes.

Example 3 Electrical Impedance Mapping of Electroporated Domains

In order to illustrate the ability of EIT to monitor electroporation intissue we have solved a mathematical simulation of the problem.

To provide the necessary data for electroporation imaging simulation, asimulated tissue phantom was created first using a 2-D fine-mesh FEMmodel (˜600 nodes, ˜3100 elements). The phantom, shown in FIG. 9,consisted of a circular imaging domain (20 mm radius, resistivity 500ohm cm for muscle with a variable number of point source electrodesequally spaced around the periphery. Within this imaging region, asingle arbitrarily shaped electroporated region was defined with adifferent resistivity. An opposite electrode current injection patternwas used, providing N(N−1)/2 independent voltage measurements where N isthe number of electrodes. The model was solved using the adaptive meshgeneration and FEM solution algorithms available in MATLAB's PartialDifferential Equation Toolbox (The Mathworks Inc.). An example mesh forthe given geometry is shown in FIG. 9. The information that the phantommodule makes available to the reconstruction algorithms represents datathat would have been available during the electroporation part of anexperiment, i.e current and voltage at the different electrodes aroundthe tissue. From this data we attempted to reconstruct the originalimage of the tissue that was input in the model. (It should be notedthat a DC injection current was used in place of the AC current typicalto EIT in order to simplify the problem. The AC derivation andimplementation is a straightforward extension of that presented here.) Atypical example for the voltage and current distribution in the phantomduring a simulated data acquisition step for an 8-electrode EIT systemis illustrated in FIG. 10.

The data obtained from the phantom was input into two EIT imagingalgorithms, one using the finite element method and the second theboundary element method to generate the impedance image. The algorithmsuse a standard Newton Raphson technique to produce the image. FIG. 11compares the image of a circular domain with two different electricalimpedances in comparison to the image of the original phantom asrecreated with the finite element technique and with the boundaryelement technique.

Electrical impedance tomography can be used to image the electroporatedregion in tissue because EIT produces an image of the tissue from a mapof the electrical impedance of the tissue and electroporation produceschanges in impedance. The electrodes for tissue electroporation imagingmay be different than those used for the electroporation process itselfor may be the same.

Example 4 Electrical Detection of Change in Membrane Permeability

As part of our research on cell electroporation we have studied theelectrical characteristics of cells during reversible and irreversibleelectroporation. In reversible electroporation the cell is not damagedby the electroporation process and the membrane reseals. In irreversibleelectroporation the cell membrane is damaged and does not reseal. In aset of experiments in which we have used ND-1 cells to measure currentsthrough cells in the micro-electroporation chip we have obtained resultsillustrated by FIGS. 8a and 8 b. The results were obtained by exposingcells to triangular shaped electrical pulses (top curve) in 8 a and 8 b.The electrical currents flowing through the cells are shown in thebottom curve in 8 a and 8 b. FIG. 8a is for a cell that was irreversibleelectroporated and FIG. 8b for a cell that was reversibleelectroporated. It can be easily noted that when the voltage was reducedin the reversible electroporated cell it retained the same values asduring the voltage increase stage. However, in the irreversible case thecurrent through the cell with the damaged membrane had a higher currentthan in the intact cell. This leads to the conclusion that electricalcurrents flowing through cells can provide indication on changes inmembrane permeability in general and a measure of the integrity of thecell membrane in particular under a variety of situations and not onlyduring electroporation. For instance, cell viability is often measuredwith trypan blue or fluorescence dyes that penetrate through damagedmembranes. These results show that an alternative method for detectingcells with damaged membranes would be to measure the electricalcurrent-voltage relation across the cell. Similarly, there are compoundsthat induce pores in the cell membrane, such as ionophors. Measuring thecurrent-voltage (impedance relation across a cell membrane could alsodetect if the membrane was impaired by these chemicals). Electricalmeasurements would have advantage over chemical means for detecting cellmembrane damage because they would produce immediate information. Apossible method for detecting changes in cell membrane permeability andin particular damaged cell membranes is to use the electroporation chipas described for the process of electroporation. The measure of damagewould be the difference between an intact cell impedance and a damagedcell impedance as illustrated in FIGS. 8a and 8 b. In tissue it would bepossible to detect cells with damaged membranes in a similar way to themethods for detection of electroporation described here.

While the present invention has been described with reference to thespecific embodiments thereof, it should be understood by those skilledin the art that various changes may be made and equivalents may besubstituted without departing from the true spirit and scope of theinvention. In addition, many modifications may be made to adapt aparticular situation, material, composition of matter, process, processstep or steps, to the objective, spirit and scope of the presentinvention. All such modifications are intended to be within the scope ofthe claims appended hereto.

What is claimed is:
 1. A method, comprising the steps of: sending anelectrical current between a first point and a second point separatedfrom the first point by an electrically conductive medium comprisingtissue; creating an image of the tissue wherein the image is based onelectrical impedance of the tissue; adjusting an electrical parameterbased on the image to obtain a desired degree of electroporation ofbiological cells in the tissue.
 2. The method of claim 1, wherein theelectrical parameter is selected from the group consisting of current,voltage and a combination of current and voltage.
 3. The method of claim1, further comprising: placing a material in the electrically conductivemedium, and adjusting the electrical current, based on the image, in amanner which moves the material into biological cells in the tissue. 4.The method of claim 3, wherein the tissue is present in a livingorganism.
 5. The method of claim 4, wherein the organism is an animal.6. The method of claim 5, wherein the organism is a human.
 7. The methodof claim 1, wherein the image is created using electrical impedancetomography.
 8. The method of claim 1, wherein the image is an impedanceimage created from known current inputs and measured input voltage usinga reconstruction algorithm.
 9. The method of claim 1, wherein the imageis an impedance image created from a known voltage input.
 10. The methodof claim 1, wherein the image is an impedance image created from ameasured current input.
 11. The method of claim 1, wherein the image isan impedance image created from a combination of a known voltage inputand a measured current input.
 12. A device, comprising: a means forcreating an electrical current across an electrically conductive medium;a means for analyzing a first electrical parameter of the electricallyconductive medium in order to create an image; a means for adjusting asecond electrical parameter based on the image to obtain a desireddegree of electroporation of biological cells in the electricallyconductive medium.
 13. The device of claim 12, wherein the firstelectrical parameter is electrical impedance.
 14. The device of claim12, wherein the second electrical parameter is selected from the groupconsisting of current, voltage and a combination of current and voltage.15. The device of claim 12, wherein the means for creating electricalcurrent comprises electrodes.